U.S. patent application number 11/351913 was filed with the patent office on 2006-08-17 for reprogrammable fluid delivery system and method of use.
Invention is credited to Christopher S. Brockman, Jacob C. Foor, David E. Hershberger, Michael Strickler, Jason D. Toman, Mark A. Wasserman.
Application Number | 20060184121 11/351913 |
Document ID | / |
Family ID | 36581706 |
Filed Date | 2006-08-17 |
United States Patent
Application |
20060184121 |
Kind Code |
A1 |
Brockman; Christopher S. ;
et al. |
August 17, 2006 |
Reprogrammable fluid delivery system and method of use
Abstract
A fluid delivery system is provided for delivering fluid to a
patient. The system comprises a reservoir for storing the fluid to
be delivered to the patient and a fluid discharge device
operatively coupled to the reservoir for delivering the fluid from
the reservoir to the patient. A controller is configured to operate
the fluid discharge device. An input device is in electronic
communication with the controller and configured for setting at
least one operating parameter of the system. The controller
operates the fluid discharge device based on the at least one
operating parameter and locks the system after the at least one
operating parameter is set such that the at least one operating
parameter is unable to be modified. A display is in electronic
communication with the controller to at least periodically display
a code for resetting the at least one operating parameter. The code
is altered at least once during use. The controller is further
configured to unlock the system upon receiving the code thereby
allowing a user to reset the at least one operating parameter.
Inventors: |
Brockman; Christopher S.;
(Kalamazoo, MI) ; Wasserman; Mark A.; (Delton,
MI) ; Hershberger; David E.; (Kalamazoo, MI) ;
Foor; Jacob C.; (Mattawan, MI) ; Strickler;
Michael; (Richland, MI) ; Toman; Jason D.;
(Swissvale, PA) |
Correspondence
Address: |
HOWARD & HOWARD ATTORNEYS, P.C.
THE PINEHURST OFFICE CENTER, SUITE #101
39400 WOODWARD AVENUE
BLOOMFIELD HILLS
MI
48304-5151
US
|
Family ID: |
36581706 |
Appl. No.: |
11/351913 |
Filed: |
February 10, 2006 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
60652454 |
Feb 11, 2005 |
|
|
|
Current U.S.
Class: |
604/151 ;
604/250 |
Current CPC
Class: |
A61M 5/172 20130101;
A61M 5/14244 20130101; A61M 2209/045 20130101; A61M 2205/505
20130101; A61M 5/14216 20130101 |
Class at
Publication: |
604/151 ;
604/250 |
International
Class: |
A61M 1/00 20060101
A61M001/00; A61M 5/00 20060101 A61M005/00 |
Claims
1. A system for delivering fluid to a patient, comprising: a
reservoir for storing the fluid to be delivered to the patient; a
fluid discharge device operatively coupled to said reservoir for
delivering the fluid from said reservoir to the patient; a
controller configured for operating said fluid discharge device; an
input device in electronic communication with said controller and
configured for setting at least one operating parameter of said
system wherein said controller operates said fluid discharge device
based on said at least one operating parameter and locks said
system after said at least one operating parameter is set such that
said at least one operating parameter is unable to be modified; and
a display in electronic communication with said controller and
configured for at least periodically displaying a code wherein said
code is altered on said display at least once during use of said
system, said controller being further configured for unlocking said
system upon receiving said code thereby allowing a user to reset
said at least one operating parameter.
2. A system as set forth in claim 1 wherein said code is associated
with said at least one operating parameter.
3. A system as set forth in claim 2 wherein said at least one
operating parameter includes a value and said code comprises at
least a portion of said value.
4. A system as set forth in claim 1 wherein said input device is
configured for setting a plurality of operating parameters, each of
said plurality of operating parameters having a value and said code
comprising at least a portion of each of said values.
5. A system as set forth in claim 4 wherein said plurality of
operating parameters includes concentration, flow rate, bolus
amount, and bolus lockout time.
6. A system as set forth in claim 5 including a countdown timer for
counting down said bolus lockout time wherein said code is based on
said countdown timer and is altered as said countdown timer changes
time.
7. A system as set forth in claim 1 wherein said code is
continuously displayed on said display.
8. A system as set forth in claim 7 wherein said code is altered at
predetermined time intervals.
9. A system as set forth in claim 1 including a housing for
supporting said reservoir, said fluid discharge device, said
controller, and said input device.
10. A system as set forth in claim 1 wherein said input device
includes at least one touch sensitive element for entering said
code into said controller using said input device.
11. A system as set forth in claim 1 wherein said system is
portable and configured to be carried by a patient.
12. A system as set forth in claim 1 wherein said input device is
configured for setting a plurality of operating parameters, each of
said plurality of operating parameters having a value and said code
being displayed on said display in a predetermined pattern that
includes at least a portion of each of said values.
13. A method of delivering fluid to a patient from a fluid delivery
system, said method comprising the steps of: setting at least one
operating parameter of the system; locking the system after setting
the at least one operating parameter such that the at least one
operating parameter is unable to be modified; delivering the fluid
from the fluid delivery system to the patient based on the setting
of the at least one operating parameter and while the system is
locked; displaying a code at least periodically on the system;
altering the code displayed at least once while delivering the
fluid to the patient; inputting the code into the system after the
code has been displayed; and unlocking the system upon inputting
the code into the system thereby allowing a user to reset the at
least one operating parameter.
14. A method as set forth in claim 13 wherein inputting the code
into the system includes entering the code using an input device
and transmitting the entered code to a controller.
15. A method as set forth in claim 13 wherein displaying the code
at least periodically on the system is further defined as
continuously displaying the code on a display of the system.
16. A method as set forth in claim 13 including setting a plurality
of operating parameters of the system and associating the code with
each of the plurality of operating parameters.
17. A method as set forth in claim 13 including relocking the
system after the user has reset the at least one operating
parameter.
18. A system for delivering fluid to a patient, comprising: a
reservoir for storing the fluid to be delivered to the patient; a
fluid discharge device including a fluid conduit for delivering the
fluid from said reservoir and through said fluid conduit to the
patient; a controller configured for operating said fluid discharge
device; and a detection circuit including at least one thermal
element thermally coupled to said fluid conduit wherein said
controller measures a first value of a measurable parameter of said
detection circuit in a first condition and a second value of said
measurable parameter in a second condition and said controller is
configured for determining the presence of fluid moving through
said fluid conduit based on said first and second values.
19. A system as set forth in claim 18 wherein measurable parameter
is a voltage of said detection circuit and said controller measures
said first value of said voltage when said fluid discharge device
is not operating to deliver the fluid through said fluid conduit
and said controller measures said second value of said voltage when
said fluid discharge device is operating to deliver the fluid
through said fluid conduit such that said controller can determine
a drop in voltage between said first and second conditions and
correlate said drop in voltage to the amount of fluid moving
through said fluid conduit.
20. A system for delivering fluid to a patient, comprising: a
housing; a reservoir supported by said housing for storing the
fluid to be delivered to the patient; a fluid discharge device
operatively coupled to said reservoir for delivering the fluid from
said reservoir to the patient; a delivery port in fluid
communication with said fluid discharge device for receiving the
fluid from said fluid discharge device and directing the fluid to
the patient; and a refill valve in fluid communication with said
reservoir and including a valve body snap-locked to said housing
and a septum member for receiving a fluid filling device to refill
said reservoir with fluid.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application claims the benefit of U.S. provisional
patent application Ser. No. 60/652,454, filed on Feb. 11, 2005, the
advantages and disclosure of which are hereby incorporated by
reference.
FIELD OF THE INVENTION
[0002] The present invention relates generally to a fluid delivery
system for delivering fluid such as medication to a patient. The
fluid delivery system is primarily used throughout the medical
profession to deliver pain control medication and other medications
subcutaneously or percutaneously to the patient after a surgical,
or some other medical, procedure. More specifically, the present
invention relates to the fluid delivery system being reprogrammed
using a security code.
BACKGROUND OF THE INVENTION
[0003] Fluid delivery systems for medical use are well known in the
art. Typically, these systems are used to deliver pain control
medication and other medications such as insulin to a patient. A
typical system includes a reservoir for storing the fluid to be
delivered to the patient and a pump assembly in operative
communication with the reservoir for delivering the fluid from the
reservoir to the patient. Often, a controller is programmed to
operate the pump assembly based on a plurality of operating
parameters such as flow rate, bolus amount, and the like. An input
device in electronic communication with the controller is used to
set values for the plurality of operating parameters. Once set, the
controller operates the pump assembly based on the operating
parameters. In many prior art systems, once the values of the
operating parameters are established, the system is locked to
prevent further access to reset the values of the operating
parameters. In some cases, however, it may be desirable to reset
the operating parameters such as when the patient requires
additional medication.
[0004] For instance, in U.S. Pat. No. 6,740,075 to Lebel et al., an
implantable infusion pump is disclosed that has certain operating
parameters that may be reset based on changing conditions. One such
operating parameter is a diagnostic medication delivery rate. In
Lebel et al., the pump communicates with an external device that
requires a password in order to change the diagnostic medication
delivery rate. The password may be established by a medical
professional using the external device, or may be a factory
password derived from the system. The factory password may be fixed
or variable. If variable, the password may be based on a variable
parameter such as the date and/or time reflected on the external
device. However, Lebel et al. does not disclose a system that takes
care to ensure that the user, e.g., the medical professional, will
not forget the password.
[0005] Therefore, there is a need in the art for a fluid delivery
system that is capable of being reprogrammed to reset values for a
plurality of operating parameters using a security code that is
easily remembered by the user.
BRIEF SUMMARY OF THE INVENTION AND ADVANTAGES
[0006] The present invention provides a fluid delivery system for
delivering fluid to a patient. The system comprises a reservoir for
storing the fluid to be delivered to the patient and a fluid
discharge device operatively coupled to the reservoir for
delivering the fluid from the reservoir to the patient. A
controller is configured for operating the fluid discharge device.
An input device is in electronic communication with the controller
and configured for setting at least one operating parameter of the
system. The controller operates the fluid discharge device based on
the at least one operating parameter and locks the system after the
at least one operating parameter is set such that the at least one
operating parameter is unable to be modified. In some cases,
however, it is desirable to reset the at least one operating
parameter. A display is electronically coupled to the controller to
at least periodically display a code for resetting the at least one
operating parameter. The code is altered by the controller at least
once during use of the system such that the code is variable. The
controller is further configured to unlock the system upon
receiving the code thereby allowing a user to reset the at least
one operating parameter.
[0007] In another embodiment, the code is continuously displayed on
the display and altered at predetermined time intervals.
[0008] In yet another embodiment of the present invention, the code
is associated with values set for a plurality of operating
parameters and displayed on the display in a predetermined
pattern.
[0009] A method of delivering fluid to the patient from the system
is also provided. The method comprises the steps of setting the at
least one operating parameter of the system and locking the system
after setting the at least one operating parameter such that the at
least one operating parameter is unable to be modified. Fluid is
delivered to the patient based on the setting of the at least one
operating parameter and while the system is locked. The code is at
least periodically displayed and altered at least once during use.
The system is unlocked upon receiving the code thereby allowing the
user to reset the at least one operating parameter.
[0010] By using the code that is at least periodically displayed on
the display and altered at least once during use, the user can more
easily remember the code to reset the at least one operating
parameter. As a result, instead of users, such as medical
professionals, being required to remember different codes for
different patients, or instead of using the same code for all
systems, the present invention provides a security code that is
easily recognized by the user. The present invention allows for
reprogramming the system, while maintaining a certain aspect of
security by altering the code at least once during use.
BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS
[0011] Advantages of the present invention will be readily
appreciated as the same becomes better understood by reference to
the following detailed description when considered in connection
with the accompanying drawings wherein:
[0012] FIG. 1A is a perspective view of a fluid delivery system
according to the present invention with an infusion tube set;
[0013] FIG. 1B is a perspective view of an underside of the system
illustrating a system mounting clip for securing the system to a
patient;
[0014] FIG. 2 is an exploded perspective view of the system
illustrating a reservoir, a base, reservoir casings, a pump
assembly, and a carrying strap of the system;
[0015] FIG. 3 is an exploded perspective view of the system
illustrating a port, a plunger, the pump assembly including a motor
and first and second pinch levers, an actuator, and the base
including an integral storage cavity for the carrying strap;
[0016] FIG. 4 is an exploded perspective view of the system
illustrating an underside of a cover, an input device, an
electronic controller and display, and a detection film having a
cantilever portion;
[0017] FIG. 5 is an exploded perspective view of the pump
assembly;
[0018] FIG. 6A is a partially cross-sectional side view of a
camshaft, the pump assembly, and the first and second pinch levers
illustrating the pinch levers in a closed position to pinch
medication inlet and outlet tubes;
[0019] FIG. 6B is a partially cross-sectional side view of the
system, as disclosed in FIG. 6A, illustrating the first pinch lever
in an open position and the second pinch lever in a closed position
to draw medication into the pump assembly;
[0020] FIG. 6C is a partially cross-sectional side view of the
system, as disclosed in FIG. 6A, illustrating the first pinch lever
in a closed position and the second pinch lever in an open position
to displace medication from the pump assembly;
[0021] FIG. 6D is a partially cross-sectional side view of the
system, as disclosed in FIG. 6A, in combination with the plunger
and the actuator, with the actuator retaining the pinch levers in
the open position;
[0022] FIG. 7 is a partially cross-sectional side view of the pump
assembly;
[0023] FIG. 8 is an exploded perspective view of the port and the
plunger;
[0024] FIG. 9 is an enlarged partially cross-sectional top view of
the plunger disposed in the port illustrating a first, second, and
third fluid connector;
[0025] FIG. 10 is a partially cross-sectional side view taken along
line 10-10 in FIG. 9 illustrating a seal disposed about the plunger
being depressed by leak ribs extending from the port;
[0026] FIG. 11A is a partially cross-sectional top view of the
system with the plunger in an off-position;
[0027] FIG. 11B is a partially cross-sectional view of the port and
the plunger disposed in the port in the off-position from FIG.
11A;
[0028] FIG. 12A is a partially cross-sectional top view of the
system with the plunger in a fill-position such that the system can
be sterilized and filled with medication;
[0029] FIG. 12B is a partially cross-sectional view of the port and
the plunger disposed in the port in the fill-position from FIG. 12A
additionally illustrating a syringe for moving the plunger into the
fill-position and a fluid cap for sterilization;
[0030] FIG. 13A is a partially cross-sectional top view of the
system with the plunger in a fluid delivery-position such that the
medication can be delivered to the patient;
[0031] FIG. 13B is a partially cross-sectional view of the port and
the plunger disposed in the port in the fluid delivery-position
from FIG. 13A additionally illustrating a connector from the
infusion tube set;
[0032] FIG. 14A is an enlarged perspective view of the
actuator;
[0033] FIG. 14B is a perspective view of an alternative embodiment
for the actuator including a control contact disposed at a distal
end of an actuation arm;
[0034] FIG. 15A is a partially cross-sectional side view of a
blockage detection system according to the present invention when
the medication outlet tube is in a normal condition;
[0035] FIG. 15B is a partially cross-sectional side view of the
blockage detection system of FIG. 15A when the medication outlet
tube is in an expanded condition due to a blockage;
[0036] FIG. 16 is a perspective view of a support platform with the
medication inlet and outlet tubes;
[0037] FIG. 17 is a schematic view of an empty detection system of
the present invention;
[0038] FIG. 18A is a top perspective view of the system engaged
with a testing instrument for confirming proper operation of the
system after assembly and prior to use;
[0039] FIG. 18B is a bottom perspective view of the system engaged
with a second testing instrument for confirming proper operation of
the system after assembly and prior to use;
[0040] FIG. 19 is a perspective view of the patient using the
carrying strap as a shoulder strap to carry the system;
[0041] FIG. 20 is an enlarged top perspective view of the integral
storage cavity defined within the base of the system;
[0042] FIG. 21 is a block diagram schematically illustrating a
control system;
[0043] FIG. 22 is an electrical diagram illustrating portions of a
watchdog circuit of the control system;
[0044] FIG. 23 is an electrical diagram illustrating further
portions of the watchdog circuit of the control system;
[0045] FIG. 24 illustrates a top view of the system with set-up
instructions on an overlay label for programming the system;
[0046] FIGS. 25A-25F illustrate various views of the display of the
system for setting a plurality of operating parameters;
[0047] FIG. 26 illustrates a scheme for displaying a code on the
display of the system;
[0048] FIGS. 27A-27B illustrate various views of the display for
unlocking the system after the plurality of operating parameters
have been set;
[0049] FIG. 28 is a perspective view of a bottom side of the system
indicating a position of a refill port of the system;
[0050] FIG. 29 is an exploded view of a valve used as the refill
port of the system;
[0051] FIG. 30 is a cross-sectional view of the valve;
[0052] FIG. 31 is a perspective assembly view of the valve and the
base;
[0053] FIG. 32 is a perspective view of the valve and the base;
[0054] FIGS. 33-35 are various views of the valve inserted in the
base in an unlocked position;
[0055] FIGS. 36-38 are various views of the valve inserted in the
base in a locked position; and
[0056] FIG. 39 is a perspective assembly view of the valve, a
flanged connector for the valve, and the reservoir of the
system
DETAILED DESCRIPTION OF THE INVENTION
[0057] Referring to the Figures, wherein like numerals indicate
like or corresponding parts throughout the several views, a fluid
delivery system is generally disclosed at 10. The fluid delivery
system 10, hereinafter described as the system 10, delivers fluid
such as medication to a patient 12 (refer to FIG. 19). Other fluids
such as saline, nutrient-enriched fluids, and the like could also
be delivered to the patient using the system 10. For purposes of
illustration, the system 10 shall be described as being used to
deliver pain control medication and other medications to the
patient 12 after a surgical, or some other medical, procedure. As
disclosed in FIG. 1A, the system 10 is used in combination with an
infusion tube set 14 to deliver the medication to the patient 12.
Typically, the infusion tube set 14 would attach to a catheter (not
shown) inserted into the patient at an infusion site to deliver
medication from the system 10 to the infusion site.
[0058] The system 10 of the present invention is suitable for
complete sterilization by a sterilization fluid including, but not
limited to, ethylene oxide (EtO) gas. Additionally, certain liquids
may be used to sterilize the system 10. For descriptive purposes
only, the terminology of "medication" and or "sterilization" fluid
may also be described throughout simply as fluid.
[0059] Referring primarily to FIGS. 2-4, the system 10 includes a
housing 16. The housing 16 comprises a base 18, a middle housing 20
mounted to the base 18 and a cover 22. The base 18, middle housing
20, and cover 22 are preferably mounted together via screws 23. The
system 10 also includes a reservoir 24 supported by the base 18 and
disposed about the middle housing 20. The reservoir 24 stores the
supply of medication that is to be delivered to the patient 12.
Preferably, the reservoir 24 is formed of a flexible, yet durable,
plastic material. The system 10 further includes a reservoir casing
26 disposed between the base 18 and the cover 22. The reservoir
casing 26 at least partially surrounds the reservoir 24 to protect
the medication that is to be delivered to the patient 12. The
preferred embodiment of the present invention includes two
reservoir casings 26 that surround the reservoir 24 to protect the
medication. Of course, it is to be understood that the reservoir
casing 26 may be a unitary component and still adequately surround
the reservoir 24 to protect the medication. The system 10 is
portable and the reservoir casings 26 are particularly useful when
the patient 12 is carrying the system 10
[0060] Referring primarily to FIGS. 2, 3, and 5-6D, a pump assembly
28 is supported by the base 18. Specifically, the pump assembly 28
is mounted to the base 18. As understood by those skilled in the
art, the pump assembly 28 is responsible for delivering the
medication to the patient 12. More specifically, the pump assembly
28 is operatively coupled to the reservoir 24 to deliver the
medication from the reservoir 24 to the patient 12. As described
below, the pump assembly 28 also serves to prevent inadvertent
delivery of the medication to the patient 12. The description of
the pump assembly 28 below is only one embodiment of a fluid
discharge device that could be used with the system 10. Other fluid
discharge devices could also be used with the system 10 to deliver
the medication to the patient 12. The pump assembly 28 is also
described in U.S. Pat. No. 6,679,862 to Diaz et al., hereby
incorporated by reference.
[0061] As disclosed best in FIG. 5, the pump assembly 28 includes a
pump housing 30 having a pump inlet 32 and a pump outlet 34. The
pump housing 30 also has at least one detent 36. The at least one
detent 36 is described below. The pump inlet 32 and the pump outlet
34 alternate between an open and a closed state to deliver the
medication to the patient 12. Referring now to FIGS. 3, and 6A-6D,
a first pinch lever 38, also referred to as a pinch valve, is
disposed at the pump inlet 32 and a second pinch lever 40 or valve
is disposed at the pump outlet 34. The first pinch lever 38
functions to alternate the pump inlet 32 between the open and the
closed state, and the second pinch lever 40 functions to alternate
the pump outlet 34 between the open and the closed state.
[0062] As FIGS. 6B and 6C disclose, the first pinch lever 38 is
moveable between an open position (FIG. 6B) and a closed position
(FIG. 6C) to control a flow of the medication into the pump housing
30 through the pump inlet 32, and the second pinch lever 40 is
moveable between an open position (FIG. 6C) and a closed position
(FIG. 6B) to control a flow of the medication from the pump housing
30 through the pump outlet 34. The pump assembly 28 further
includes a motor 42 operatively engaging the first and second pinch
levers 38, 40 for moving these levers 38, 40 into the open position
such that the medication can be delivered to the patient 12. The
motor 42 includes a driving output shaft, not shown in the Figures,
for driving the pump assembly 28. A power source 43 is integrated
into the system 10 to provide power to the system 10, including the
motor 42. Preferably, the power source includes batteries 45 and
battery contacts 47.
[0063] As shown in FIG. 6A, the first pinch lever 38 is
normally-biased to maintain the pump inlet 32 in the closed state
and the second pinch lever 40 is normally-biased to maintain the
pump outlet 34 in the closed state. To accomplish this, at least
one biasing device 44 is included in the pump assembly 28. In one
embodiment of the present invention, the at least one biasing
device 44 comprises a first 46 and a second 48 compression spring.
The first compression spring 46, engages the first pinch lever 38,
and the second compression spring 48, engages the second pinch
lever 40. As disclosed in FIG. 6A, the first 46 and second 48
compression springs maintain the first and second pinch levers 38,
40 in the closed position during failure of the motor 42 thereby
preventing the inadvertent delivery of the medication to the
patient 12. More specifically, the closed first pinch lever 38
prevents the medication from being drawn into the pump assembly 28
through the pump inlet 32, and the closed second pinch lever 40
prevents the medication from being displaced from the pump assembly
28 through the pump outlet 34.
[0064] Referring primarily to FIGS. 5-6D, to effectively operate
the system 10 and move the first and second pinch levers 38, 40 for
delivery of the medication to the patient 12, the pump assembly 28
of the present invention further includes a camshaft 50 supported
on the pump housing 30. The camshaft 50 is geared to the motor 42,
via a number of gears 52, to operatively couple the motor 42 to the
first and second pinch levers 38, 40. The camshaft 50 is described
in greater detail below.
[0065] As disclosed best in FIGS. 5 and 7, the pump assembly 28
also includes a piston 54 disposed in the pump housing 30. The
motor 42 moves the piston 54 within the pump housing 30 to draw the
medication into the pump housing 30 when the first pinch lever 38
is in the open position and the second pinch lever 40 is in the
closed position (see FIG. 6B). The motor 42 also moves the piston
54 within the pump housing 30 to displace the medication from the
pump housing 30 when the first pinch lever 38 is in the closed
position and the second pinch lever 40 is in the open position (see
FIG. 6C). The piston 54 includes an actuation end 56 and a pumping
end 58. A diaphragm seal 60 is disposed at the pumping end 58 of
the piston 54. The diaphragm seal 60 is secured at the pumping end
58 of the piston 54 by a piston cap 62. The piston 54 also includes
at least one slot 63 at the actuation end 56. The at least one
detent 36 of the pump housing 30, originally introduced above,
engages the at least one slot 63 at the actuation end 56 of the
piston 54 to prevent unwanted rotation of the piston 54 as the
piston 54 is moved within the pump housing 30 by the motor 42 and
the camshaft 50.
[0066] The camshaft 50 supports first and second outside cams 64,
66 and an inside cam 68. The inside cam 68 of the camshaft 50 is
disposed between the first and second outside cams 64, 66. The
first outside cam 64 engages the first pinch lever 38 to move the
first pinch lever 38 between the open and closed position, and the
second outside cam 66 engages the second pinch lever 40 to move the
second pinch lever 40 between the open and closed positions. The
inside cam 68 engages the actuation end 56 of the piston 54 to move
the piston 54 within the pump housing 30.
[0067] Referring to FIG. 5, the first and second outside cams 64,
66 include a plurality of slits 70 along an outer circumference 72
of the cams 64, 66. These slits 70 are used during assembly and
testing of the system 10 to confirm dimensional tuning of the cams
64, 66. Also, at least one of the first and second outside cams 64,
66, preferably the first outside cam 64, includes an assembly slot
74 defined within the outer circumference 72 of the cams 64, 66.
This assembly slot 74 facilitates assembly of the pump assembly 28.
In particular, this assembly slot 74 facilitates mounting of the
camshaft 50, including the cams 64, 66, after the first and second
pinch levers 38, 40 have already been incorporated into the system
10.
[0068] Each of the first and second pinch levers 38, 40 comprise a
cam follower 76 and lever guides 78. The lever guides 78 are
described below. The cam followers 76 of the pinch levers 38, 40
are engaged by the camshaft 50 for alternating movement of the
first and second pinch levers 38, 40 between the open and closed
positions such that the medication can be delivered to the patient
12. More specifically, the cam follower 76 of the first pinch lever
38 is engaged by the first outside cam 64 for alternating movement
of the first pinch lever 38 between the open and closed positions,
and the cam follower 76 of the second pinch lever 40 is engaged by
the second outside cam 66 for alternating movement of the second
pinch lever 40 between the open and closed positions. Even more
specifically, each of the first and second outside cams 64, 66
include internal cam surfaces 80. As disclosed in FIGS. 6A-6D, the
cam follower 76 of the first pinch lever 38 rides within the
internal cam surface 80 of the first outside cam 64 for alternating
movement of the first pinch lever 38, and the cam follower 76 of
the second pinch lever 40 rides within the internal cam surface 80
of the second outside cam 66 for alternating movement of the second
pinch lever 40.
[0069] Referring primarily to FIGS. 3, and 8-10, the system 10
further includes a port assembly 82 that enables various fluids,
such as the medication or the sterilization fluid, to flow into,
from, and within the system 10. The port assembly 82, hereinafter
described as the port 82, extends from the middle housing 20. The
port 82 is in fluid communication with the reservoir 24 and the
pump assembly 28. During sterilization, the port 82 provides access
for the sterilization fluid to flow into the reservoir 24 and the
pump assembly 28. During filling, the port 82 provides access for
the medication to flow into the reservoir 24 and the pump assembly
28. During delivery of the medication to the patient 12, the port
82 provides access for the medication to be delivered to the
patient 12.
[0070] Referring particularly to FIGS. 9, and 11A-13B, the port 82
includes an elongated housing 84. The elongated housing 84 includes
a proximal end 86, a distal end 88, and an interior wall 90
defining a fluid chamber 92 between the proximal and distal ends
86, 88. It is the proximal end 86 of the elongated housing 84 that
extends from the system 10 to provide access for the fluid to flow
both into and from the system 10. The port 82 further includes a
first fluid connector 94, a second fluid connector 96, and a third
fluid connector 98. The first fluid connector 94, alternatively
referred to as an outlet of the port 82, extends from the elongated
housing 84 to allow the fluid to flow from the fluid chamber 92
into the pump assembly 28. The second fluid connector 96,
alternatively referred to as an inlet to the port 82, extends from
the elongated housing 84 to allow the fluid to flow from the pump
assembly 28 into the fluid chamber 92. The third fluid connector
98, alternatively referred to as an access to the reservoir 24,
extends from the elongated housing 84 to allow the fluid to flow
between the fluid chamber 92 and the reservoir 24. In the preferred
embodiment of the present invention, there are two third fluid
connectors 98, one third fluid connector 98 extending from opposite
sides of the elongated housing 84.
[0071] Referring primarily to FIGS. 3, 6D, 8-10, and 11A-13B, the
port 82 further includes a plunger 100. The plunger 100 is disposed
in the fluid chamber 92 of the port 82 and is moveable between an
off-position (FIGS. 11A-11B), a fill-position (FIGS. 12A-12B), and
a fluid delivery-position (FIGS. 13A-13B). As disclosed in FIGS.
11A-11B, in the off-position, the first, second, and third fluid
connectors 94, 96, 98 are isolated from the proximal end 86 of the
elongated housing 84 by the plunger 100. As a result, the flow of
fluid through the port 82 is prevented. As disclosed in FIGS.
12A-12B, in the fill-position, the first and third fluid connectors
94, 98 are in fluid communication with the proximal end 86 of the
elongated housing 84. As a result, a fluid flow path, shown but not
numbered in FIGS. 12A-12B, is provided between the proximal end 86
of the elongated housing 84, the medication reservoir 24, and the
pump assembly 28 such that the fluid can be filled through the
proximal end 86 of the housing and into the medication reservoir 24
and the pump assembly 28. This fluid flow path is defined between
the port 82, the reservoir 24, and the pump assembly 28 such that
the flow of sterilization fluid through the fluid flow path is
continuous during sterilization of the system 10. The fill-position
of the plunger 100 is utilized when the system 10 is being
sterilized with the sterilization fluid and also when the system 10
is being filled with medication. As disclosed in FIGS. 13A-13B, in
the fluid delivery position, the first, second, and third fluid
connectors 94, 96, 98 are in fluid communication with the proximal
end 86 of the elongated housing 84 and with each other for
supplying the pump assembly 28 and for delivering the fluid to the
patient 12.
[0072] Referring particularly to FIGS. 3, and 8-10, the port 82 and
the plunger 100 are described in greater detail. The plunger 100
includes a length L, a circumference C, and a plurality of seats
124 disposed along the length L and about the circumference C of
the plunger 100. The seats 124 extend outwardly from the
circumference C of the plunger 100 to the interior wall 90 of the
elongated housing 84 of the port 82 to segregate the fluid chamber
92 of the elongated housing 84. A fluid passage, not numbered, is
defined between each of the seats 124 and the interior wall 90 of
the housing. These fluid passages control the flow of fluid within
the port 82. Although the seats 124 may suitably segregate the
fluid chamber 92, it is preferred that seals 126 are disposed about
each of the seats 126 to assist with sealing the fluid passages
from one another. In the most preferred embodiment these seals are
O-rings. At least one leak rib 128 extends at least partially along
the interior wall 90 of the elongated housing 84. The at least one
leak rib 128 selectively causes at least one of the seals 126 to
leak when the plunger 100 is in the fill-position. As disclosed in
the Figures, preferably there are two leak ribs 128 that extend
along the interior wall 90 of the elongated housing 84.
[0073] As shown in FIGS. 11A-13B, the plunger 100 is at least
partially hollow. As such, the plunger 100 defines an internal
fluid bore 130 that extends within the plunger 100 between the
seats 124. The plunger 100 further includes an access end 132 and a
plunger actuation end 134. A plunger biasing device 136, preferably
a compression spring, is disposed about the plunger actuation end
134 of the plunger 100 to bias the plunger 100 into the
off-position. The internal fluid bore 130 extends from the access
end 132, where the fluid flows into and from the internal fluid
bore 130, toward the plunger actuation end 134. The internal fluid
bore 130 includes a fluid duct 138 in fluid communication with one
of the fluid passages such that the flow can flow into and from the
internal fluid bore 130.
[0074] In the most preferred embodiment of the present invention,
the plurality of seats 124 are further defined as a first, second,
third, and fourth seat 140, 142, 144, 146, respectively. The first
seat 140 is disposed toward the access end 132 of the plunger 100,
the fourth seat 146 is disposed toward the plunger actuation end
134 of the plunger 100, and the second and third seats 142, 144 are
disposed successively between the first and fourth seats 140, 146.
In this embodiment, the fluid passages are further defined as a
first, second, and third fluid passage 148, 150, 152, respectively.
The first fluid passage 148 is defined between the first and second
seats 140, 142 and the interior wall 90, the second fluid passage
150 is defined between the second and third seats 142, 144 and the
interior wall 90, and the third fluid passage 152 is defined
between the third and fourth seats 144, 146 and the interior wall
90.
[0075] A first seal 154 is disposed about the first seat 140 for
sealing the first fluid passage 148 from the access end 132 of the
plunger 100, a second seal 156 is disposed about the second seat
142 for sealing the first and second fluid passages 148, 150 from
one another, a third seal 158 is disposed about the third seat 144
for sealing the second and third fluid passages 150, 152 from one
another, and a fourth seal 160 is disposed about the fourth seat
146 for sealing the third fluid passage 152 from the plunger
actuation end 134 of the plunger 100. In this embodiment, the at
least one leak rib 128 extends along the interior wall 90 of the
elongated housing 84 from the proximal end 86 toward the distal end
88 just beyond the first seal 154 such that only the first seal 154
selectively leaks when the plunger 100 is in the fill-position.
[0076] In this most preferred embodiment, the internal fluid bore
130 extends within the plunger 100 from the access end 132 to the
third seat 144. As such, the fluid duct 138 is in fluid
communication with the second fluid passage 150 defined between the
second and third seats 142, 144 and the interior wall 90 such that
the fluid can flow into and from the internal fluid bore 130 at the
second fluid passage 150.
[0077] The off-, fill-, and fluid delivery-positions of the plunger
100 are now described in the context of this most preferred
embodiment having four seats 140, 142, 144, 146, three fluid
passages 148, 150, 152, and four seals 154, 156, 158, 160.
Referring to FIGS. 11A-11B, when the plunger 100 is in the
off-position, the first, second, and third fluid connectors 94, 96,
98 are isolated from the proximal end 86 of the elongated housing
84 and from the access end 132 of the plunger 100 by the first,
second, and third seats 140, 142, 144. In this off-position, the
first and third fluid connectors 94, 98 are aligned with the third
fluid passage 152.
[0078] Referring to FIGS. 12A-12B, when the plunger 100 is in the
fill-position, the first and third fluid connectors 94, 98 are in
fluid communication with the proximal end 86 of the elongated
housing 84 and with the access end 132 of the plunger 100 through
the second fluid passage 150 and the fluid duct 138 of the internal
fluid bore 130. In this fill-position, the first and third fluid
connectors 94, 98 are aligned with the second fluid passage 150. As
such, the fluid can be filled through the access end 132 of the
plunger 100, through the internal fluid bore 130 and the fluid duct
138, and into the reservoir 24 and the pump assembly 28. In the
fill-position, the second fluid connector 96 is isolated from the
proximal end 86 of the elongated housing 84, from the access end
132 of the plunger 100, and from the first and third fluid
connectors 94, 98 by the third and fourth seats 144, 146.
[0079] Referring to FIGS. 13A-13B, when the plunger 100 is in the
fluid delivery-position, the second fluid connector 96 is in fluid
communication with the proximal end 86 of the housing and with the
access end 132 of the plunger 100 through said second fluid passage
150 and the fluid duct 138 of the internal fluid bore 130. In the
fluid delivery-position, the medication is delivered from the pump
assembly 28 to the patient 12. In the fluid delivery-position, the
first and third fluid connectors 94, 98 are isolated from the
proximal end 86 of the housing and from the access end 132 of the
plunger 100 by the first and second seats 140, 142. However, the
first and third fluid connectors 94, 98 are in fluid communication
with the reservoir 24 through the first fluid passage 148 to supply
the pump assembly 28 with the fluid, i.e., with the medication.
That is, in the fluid delivery-position, the first and third fluid
connectors 94, 98 are aligned with the first fluid passage 148.
[0080] A fluid filling device, shown generally in FIG. 12B at 162,
engages the proximal end 86 of the housing to automatically move
the plunger 100 into the fill-position for filling the reservoir 24
and the pump assembly 28. If the system 10 is being sterilized,
then the fluid filling device 162 is preferably a fluid, or
sterilization, cap 164 (shown detached from the system 10 in FIG.
12B) that moves the plunger 100 into the fill-position to enable a
sterilization fluid to penetrate into the reservoir 24 and the pump
assembly 28. The fluid cap 164, by design, automatically moves the
plunger 100 into the fill-position. Therefore, when the system 10
is introduced into a chamber filled with the sterilization fluid,
preferably EtO gas, then the sterilization fluid flows, or seeps,
through the fluid cap 164, through the proximal end 86 of the
elongated housing 84 and the access end 132 of the plunger 100,
through the internal fluid bore 130 and the fluid duct 138, into
the second fluid passage 150, through the third fluid connector 98
into the reservoir 24, and through the first fluid connector 94
into the pump assembly 28.
[0081] If the system 10 is being filled with medication, then the
fluid filling device 162 is preferably a syringe 166 that moves the
plunger 100 into the fill-position for filling the reservoir 24 and
the pump assembly 28. The syringe 166 (shown attached to the system
10 in FIG. 12B) engages the access end 132 of the plunger 100 and,
by design, automatically moves the plunger 100 into the
fill-position for filling the reservoir 24 and the pump assembly 28
through the internal fluid bore 130. Therefore, when the system 10
is being filled, the syringe 166 interacts with the proximal end 86
of the elongated housing 84 and the access end 132 of the plunger
100 and, as the syringe plunger is depressed, the medication flows
through the internal fluid bore 130 and the fluid duct 138, into
the second fluid passage 150, through the third fluid connector 98
into the reservoir 24, and through the first fluid connector 94
into the pump assembly 28.
[0082] To deliver the medication to the patient 12, the system 10
is utilized in combination with the infusion tube set 14. Referring
back to FIG. 1A, the infusion tube set 14 includes a fluid end 168
and a patient end 170. The fluid end 168 of the tube set 14,
through a delivery connector 172, engages the proximal end 86 of
the elongated housing 84 and the access end 132 of the plunger 100
to automatically move the plunger 100 into the fluid
delivery-position for delivering the medication to the patient 12.
Therefore, as shown in FIGS. 13A-13B, when the pump assembly 28 is
operating, the medication is drawn from the reservoir 24 through
the third fluid connector 98 into the port 82 at the first fluid
passage 148, and through the first fluid connector 94 into the pump
inlet 32. The medication is then displaced out of the pump assembly
28 through the pump outlet 34, through the second fluid connector
96 into the port 82 at the second fluid passage 150, through the
fluid duct 138 and the internal fluid bore 130 of the plunger 100,
and out the access end 132 of the plunger 100 at the fluid end 168
of the infusion tube set 14. From there, the medication flows
through the infusion tube set 14, out the patient end 170, and to
the patient 12.
[0083] Referring primarily to FIGS. 3, 6D, 11A, 12A, 13A, and
14A-14B, the system 10 further includes an actuator 102 disposed in
the housing 16. The actuator 102 is moveable between a disengaged
position and an engaged position. The disengaged position of the
actuator 102 is described below. As disclosed in FIG. 6D, in the
engaged position, the actuator 102 operatively engages the pump
inlet 32 and the pump outlet 34 to retain, i.e., lock, both the
pump inlet 32 and the pump outlet 34 in the open state during
sterilization. More specifically, the actuator 102 interacts with
the first and second pinch levers 38, 40 to retain both the pump
inlet 32 and the pump outlet 34 in the open state during
sterilization. In the engaged position, the actuator 102 moves the
first pinch lever 38 away from the pump inlet 32 into the open
position to retain the pump inlet 32 in the open state, and the
actuator 102 moves the second pinch lever 40 away from the pump
outlet 34 into the open position to retain the pump outlet 34 in
the open state. The actuator 102 retains both the first and second
pinch levers 38, 40 in the open position for sterilization despite
the bias of the at least one biasing device 44. With the pump inlet
32 and the pump outlet 34 in the open state, the sterilization
fluid can penetrate throughout the entire system 10 to completely
sterilize the system 10. That is, the sterilization fluid can
penetrate into the reservoir 24, the pump inlet 32, the pump
housing 30, and the pump outlet 34 to completely sterilize the
system 10.
[0084] On the other hand, when the actuator 102 is in the
disengaged position, as indicated by the absence of the actuator
102 from FIGS. 6B-6C, the actuator 102 is operatively disengaged
from the pump inlet 32 and the pump outlet 34. The actuator 102 is
in the disengaged position when it is necessary to deliver the
medication to the patient 12 such that the pump inlet 32 and the
pump outlet 34 can alternate between the open and closed states to
deliver the medication the patient 12. Disengagement of the
actuator 102 permits the pump inlet 32 and the pump outlet 34 to
alternate between the open and closed states.
[0085] Referring particularly to FIGS. 14A-14B, the actuator 102 is
disclosed in greater detail. The actuator 102 includes a base
portion 104 and at least one engagement arm 106 extending from the
base portion 104. The at least one engagement arm 106 of the
actuator 102 operatively engages the pump assembly 28 to retain the
pump inlet 32 and the pump outlet 34 in the open state during
sterilization. In the preferred embodiment of the present
invention, the actuator 102 more specifically includes first and
second engagement arms 108, 110, respectively, extending from the
base portion 104. In the preferred embodiment, the actuator 102
also includes an actuation arm 112. The actuation arm 112 extends
from the base portion 104 between the first and second engagement
arms 108, 110. As shown in the Figures, the actuation arm 112
extends upwardly from the base portion 104 between the first and
second engagement arms 108, 110.
[0086] During sterilization, the first engagement arm 108 of the
actuator 102 engages the first pinch lever 38 to move the first
pinch lever 38 away from the pump inlet 32 to retain the pump inlet
32 in the open state. Similarly, during sterilization, the second
engagement arm 110 of the actuator 102 engages the second pinch
lever 40 to move the second pinch lever 40 away from the pump
outlet 34 to retain the pump outlet 34 in the open state.
[0087] After sterilization it is desirable to move the actuator 102
into the disengaged position such that the pump assembly 28 can
operate and the medication can be delivered to the patient 12. As
indicated by the arrow (A) in FIG. 6D, the plunger 100 moves to
displace the actuator 102 from the engaged position thereby moving
the actuator 102 into the disengaged position. To displace the
actuator 102, the plunger 100 engages the actuation arm 112. The
plunger 100 displaces the actuator 102 from the operative
engagement with the pump assembly 28, after sterilization, such
that the pump inlet 32 and the pump outlet 34 can alternate between
the open and the closed state to deliver the medication to the
patient 12. More specifically, the plunger 100 displaces the
actuator 102 from the engagement with the first and second pinch
levers 38, 40, after sterilization, such that medication can be
delivered to the patient 12. As such, the motor 42, which
operatively engages the first and second pinch levers 38, 40, can
move these levers 38, 40 for drawing the medication into the pump
housing 30 through the pump inlet 32 and for displacing the
medication from the pump housing 30 through the pump outlet 34.
[0088] Referring now to FIG. 14B, a control contact 114, preferably
a spring-like control contact 114, may be disposed at a distal end
116 of the actuation arm 112 away from the base portion 104 to
indicate to the system 10 whether the actuator 102 is in the
engaged or the disengaged position. The control contact 114
interacts with the actuation arm 112 of the actuator 102 upon the
movement of the actuator 102 between the engaged or the disengaged
position. If the control contact 114 is included, it is preferred
that when the actuator 102 is disengaged from the first and second
pinch levers 38, 40, i.e., when the actuator 102 is in the
disengaged position, it contacts the control contact 114 to active
an electronic controller 118. The electronic controller 118 is
activated to permit the pump assembly 28 to operate to deliver the
medication to the patient 12. As indicated above, it is preferred
that the actuation arm 112 of the actuator 102 is in contact with
the control contact 114 when the actuator 102 is in the disengaged
position. Of course, it is to be understood that the opposite could
be true. That is, the system 10 can be designed such that the
actuation arm 112 of the actuator 102 is in contact with the
control contact 114 when the actuator 102 is in the engaged
position.
[0089] The system 10 further includes a medication inlet tube 120
and a medication outlet tube 122. The medication inlet tube 120 is
connected between the port 82 and the pump inlet 32 to provide
access for the sterilization fluid to flow from the port 82 into
the pump assembly 28, specifically into the pump inlet 32. The
medication outlet tube 122 is connected between the pump outlet 34
and the port 82 to provide access for the sterilization fluid to
flow from the pump assembly 28, specifically from the pump outlet
34, into the port 82. The medication inlet tube 120 and the first
pinch lever 38 together establish the pump inlet 32, and the
medication outlet tube 122 and the second pinch lever 40 together
establish the pump outlet 34.
[0090] When the at least one biasing device 44 engages the first
pinch lever 38 to normally-bias the first pinch lever 38 into the
closed position, the medication inlet tube 120 is pinched. As such,
the pump inlet 32 is maintained in the closed state. Similarly,
when the at least one biasing device 44 engages the second pinch
lever 40 to normally-bias the second pinch lever 40 into the closed
position, the medication outlet tube 122 is pinched. As such, the
pump outlet 34 is maintained in the closed state. However, as
disclosed in FIG. 6D, when the actuator 102 is in the engaged
position during sterilization, the actuator 42 overcomes the bias
of the at least one biasing device 44 to move the first pinch lever
38 away from the medication inlet tube 120 such that the pump inlet
32 remains in the open state, and the actuator 102 overcomes the
bias of the at least one biasing device 44 to move the second pinch
lever 40 away from the medication outlet tube 122 such that the
pump outlet 34 remains in the open state.
[0091] Referring back to FIG. 4, the system 10 further includes the
electronic controller 118. The electronic controller 118 controls
an amount of the medication that is to be delivered to the patient
12 by controlling the pump assembly 28 as described further below.
The electronic controller 118 is mounted to a printed circuit board
119 that is attached to the cover 122. Furthermore, the electronic
controller 118 remains mounted to the cover 22 during sterilization
such that the entire system 10, including all mechanical
components, the reservoir 24, and the electronic controller 118, is
simultaneously sterilized. An electronic display 174 and an input
device 176, in the form of at least one control button 176, are
mounted in the cover 22. The electronic display 174 and the input
device 176 are in electronic communication with the electronic
controller 118 to control the amount of the medication to be
delivered to the patient 12. As with the electronic controller 118,
the electronic display 174 and the input device 176 also remain in
the housing 16 during sterilization.
[0092] The present invention also provides a blockage detection
system, which is generally disclosed at 178 in FIGS. 15A-15B. The
blockage detection system 178 detects a blockage in the flow of the
medication to the patient 12. The blockage detection system 178
comprises the housing 16, the reservoir 24, the port 82, the pump
assembly 28, the medication outlet tube 122, and the electronic
controller 118. The blockage detection system 178 also includes a
detection film 180 which is described below.
[0093] In the blockage detection system 178, the printed circuit
board 119 is mounted to the cover 22. A portion of the outlet tube
122 is mounted adjacent to the printed circuit board 119 to be
exposed to the detection film 180, which is disposed on the printed
circuit board 119. The outlet tube 122 fluidly connects the pump
assembly 28 and the port 82 to provide access for the medication to
flow from the pump assembly 28 into the port 82 and to the patient
12. The outlet tube 122 has a diameter that is contractible and
expandable between a normal condition (see FIG. 15A) and an
expanded condition (see FIG. 15B). The diameter of the outlet tube
122 contracts and expands in response to variations in pressure
that result from the flow of the medication from the reservoir 24
through the pump assembly 28 into the port 82 and to the patient
12.
[0094] As disclosed in the Figures, the outlet tube 122 is placed
in contact with the detection film 180 via a support platform 182
(see FIG. 16). That is, the support platform 182 is mounted to the
middle housing 20 and the printed circuit board 119 to support the
outlet tube 122 adjacent to the detection film 180 on the printed
circuit board 119. The support platform 182 includes at least one
tube slot 184. The at least one tube slot 184 houses the diameter
of the outlet tube 122. The outlet tube 122 is mounted in the tube
slot 184 such that the portion of the outlet tube 122 is exposed to
the detection film 180.
[0095] The detection film 180 is disposed between the printed
circuit board 119 and the outlet tube 122. The detection film 180
is in contact with the portion of the outlet tube 122 and remains
spaced from the printed circuit board 119 when the diameter of the
outlet tube 122 is in the normal condition, as in FIG. 15A. On the
other hand, the detection film 180 is in contact with the outlet
tube 122 and contacts the printed circuit board 119 when the
diameter of the outlet tube 122 is in the expanded condition, as in
FIG. 15B, in response to increased pressure resulting from the
blockage in the flow of the medication to the patient 12. More
specifically, it is preferred that an electronic switch 186 is
embedded in the printed circuit board 119 for contact by the
detection film 180. The detection film 180 interacts with the
electronic controller 118 by contacting the electronic switch 186
to transmit a corresponding signal to the electronic controller 118
when the diameter of the outlet tube 122 is in the expanded
condition.
[0096] For activating the electronic controller 118 when the
diameter of the outlet tube 122 is in the expanded condition, it is
also preferred that the detection film 180 is conductive. Once
activated by the detection film 180, the electronic controller 118
deactivates the pump assembly 28 to prevent delivery of the
medication to the patient 12 when the diameter of the outlet tube
122 is in the expanded condition. Deactivation of the pump assembly
28 prevents further blockage and further increases in pressure. To
properly ensure that the there is a blockage in the outlet tube
122, it is most preferred that the electronic controller 118, and
therefore the pump assembly 28, are deactivated only if the
diameter of the outlet tube 122 is in the expanded condition for
more than at least one or two cycles of the pump assembly 28. This
additional measure avoids false readings and the deactivation of
the pump assembly 28 when the outlet tube 122 is truly not
blocked.
[0097] Additionally, once activated by the detection film 180, the
electronic controller 118 may also activate an alarm 188, shown
schematically in the Figures. The alarm 188, which can be audible
and/or visually displayed on the electronic display 174, would
indicate the blockage that is due to the blockage in the flow of
the medication to the patient 12.
[0098] It is preferred that the detection film 180 is mounted to
the printed circuit board 119 with an adhesive layer 190. The
adhesive layer 190 also establishes a thickness that is necessary
to space the detection film 180, specifically a portion of the
detection film 180, from the electronic switch 186 when the
diameter of the outlet tube 122 is in the normal condition. The
detection film 180 contacts the electronic switch 186 to activate
the electronic controller 118 when the diameter of the outlet tube
122 is in the expanded condition in response to increased pressure
in the outlet tube 122.
[0099] Referring to FIG. 17, an empty detection system 400 is also
provided for the system 10. The empty detection system 400
determines when a supply of the medication has been depleted. The
empty detection system 400 comprises a detection circuit including
a plurality of thermal elements 402, preferably three negative
temperature coefficient (NTC) thermistors 402, preferably
positioned on the printed circuit board 119 and thermally coupled
with at least a portion of the inlet tube 120 (it should be
appreciated that the thermistors 402 may also be separate from the
printed circuit board 119, as with all electronic components
disclosed as being positioned on the printed circuit board 119). In
other embodiments, the thermistors 402 can be thermally coupled to
the outlet tube 122. The power source, e.g, the battery 45, powers
the thermistors 402 to alter their temperature, e.g., heat, the
thermistors 402 during use. Referring to FIG. 16, the portion of
the inlet tube 120 is thermally coupled to the thermistors 402 on
the printed circuit board 119 via the support platform 182. That
is, the support platform 182 is mounted to the middle housing 20
and the printed circuit board 119 to support the inlet tube 120
adjacent to the thermistors 402 on the printed circuit board 119.
The support platform 182 includes at least one tube slot 184. The
at least one tube slot 184 houses the diameter of the inlet tube
120. The inlet tube 120 is mounted in the tube slot 184 such that
the portion of the inlet tube 120 is exposed to the thermistors
402.
[0100] Referring back to FIG. 17, prior to fluid flowing through
the inlet tube 120, i.e., in a first condition of the pump assembly
28 such as when the pump assembly 28 is not operating, a voltage is
applied across the thermistors 402 and a voltage dividing resistor
404 by the battery source 45, such as 4.5 volts. The thermistors
402 are connected in series with the voltage dividing resistor 404.
The current flowing through the thermistors 402 causes them to
self-heat, thereby causing a decrease in resistance and an increase
in voltage observed across the voltage dividing resistor 404 (it
should be appreciated that depending on the type of thermistor
used, the decrease in resistance and increase in voltage may be
reversed). An amplifier 406 amplifies the voltage and sends a
corresponding amplified signal to an analog-to-digital converter
408, which then sends a corresponding digital signal to the
controller 118 for processing (specifically by a processor of the
controller 118). The controller 118 records a first value of the
voltage, or other measurable electrical parameter, as provided by
the analog-to-digital converter 408, and stores it in a memory of
the controller 118.
[0101] The heat from the thermistors 402 increases the temperature
of the medication inlet tube 120 and fluid near the thermistors
402. When the pump assembly 28 begins operating, i.e., in a second
condition of the pump assembly 28, the heated fluid near the
thermistors 402 is replaced with unheated fluid as fluid flows
through the inlet tube 120, which draws heat away from the
thermistors 402. This cooling effect increases the resistance of
the thermistors 402, which decreases the voltage observed across
the voltage dividing resistor 404. The controller 118 then records
a second value of the voltage or other measurable electrical
parameter, as provided by the analog-to-digital converter 408, and
compares the second value to the first value to determine a change,
or drop, in voltage.
[0102] As the reservoir 24 becomes empty, the cooling effect is
reduced, i.e., less fluid is carrying away heat from the medication
inlet tube 120 adjacent to the thermistors 402, and the observed
voltage drop lessens. Below a predetermined voltage threshold, or
voltage drop, the system 10 is deemed empty by the controller 118.
When the system 10 is determined to be empty, the controller 118
produces a signal which causes an empty symbol (not shown), such as
a conventional automotive fuel gauge, to be displayed on the
display 174. Fluid can then be added to the reservoir through a
refill port 300, as described further below.
[0103] Referring now to FIGS. 1B, 6A-6D, and 18A-18B, the system 10
of the present invention can be tested using a testing instrument
200 after assembly of the system 10. The system 10 is tested after
assembly and prior to shipment and use by the surgeons, patients,
and the like to confirm various operations of the system 10. In the
preferred embodiment, to test the system 10, the system 10 is
mounted onto the testing instrument 200. One operation of the
system 10 that is confirmed after assembly of the system 10 is the
operation of the pump assembly 28.
[0104] To confirm these operations, the system 10 includes at least
one testing access port 202. The at least one testing access port
202 is defined within the base 18 and is aligned with at least one
of the pump inlet 32, the pump outlet 34, and the actuator 102.
Preferably, the at least one testing access port 202 is aligned
with all three of the pump inlet 32, the pump outlet 34, and the
actuator 102. The at least one testing access port 202 provides
access for the testing instrument 200 to move the actuator 102
between the disengaged position and the engaged position. If the at
least one testing access port 202 is aligned with the pump inlet 32
and the pump outlet 34 then it is aligned with the first and second
pinch levers 38, 40, respectively. Also, as for the alignment with
the actuator 102, the at least one testing access port 202 is more
specifically aligned with the at least one engagement arm 106 of
the actuator 102. This provides access for the testing instrument
200 to move the actuator 102 between the disengaged position and
the engaged position.
[0105] The system 10 is preferably assembled with the actuator 102
in the engaged position such that the first and second pinch levers
38, 40 are in the open position and the resiliency and life of the
medication inlet and outlet tubes 120, 122 is not compromised.
Because the at least one testing access port 202 provides access
for the testing instrument 200 to move the actuator 102 between the
disengaged position and the engaged position, the testing
instrument 200 can be inserted into the at least one testing access
port 202 to disengage the actuator 102, i.e., to move the actuator
102 into the disengaged position. As such, the pump inlet 32 and
the pump outlet 34 can alternate between the open and closed states
after assembly and during testing of the system 10.
[0106] The at least one testing access port also provides access
for the testing instrument 200 such that the pump inlet 32 and the
pump outlet 34 can be retained in the open state after the system
10 has been tested to prepare the system 10 for sterilization. That
is, after the system 10 has been tested, the actuator 102 is moved
from the disengaged position back into the engaged position to
prepare the system 10 for sterilization. In the engaged position,
the first and second pinch levers 38, 40 are retained in the open
state.
[0107] In the preferred embodiment, the at least one testing access
port 202 is further defined as first, second, and third testing
access ports 204, 206, 208, respectively. The first testing access
port 204 is aligned with the pump inlet 32, the second testing
access port 206 is aligned with the pump outlet 34, and the third
testing access port 208 is aligned with the actuator 102 for
providing access to the testing instrument 200 to move the actuator
102 into the engaged position. More specifically, the first testing
access port 204 is aligned with the first pinch lever 38 such that
the first pinch lever 38 is engaged by the testing instrument 200.
Once inside the first testing access port 204, the testing
instrument 200 forces the first pinch lever 38 away from the pump
inlet 32 and forces the pump inlet 32 into the open state.
Similarly, the second testing access port 206 is aligned with the
second pinch lever 40 such that the second pinch lever 40 is
engaged by the testing instrument 200. Once inside the second
testing access port 206, the testing instrument 200 forces the
second pinch lever 40 away from the pump outlet 34 and forces the
pump outlet 34 into the open state. The first and second pinch
levers 38, 40 include the lever guides 78 opposite the cam follower
76 of each pinch lever 38, 40. To move the first and second pinch
levers 38, 40, the testing instrument 200 engages the lever guides
78 upon insertion into the first and second testing access ports
204, 206. After the testing instrument 200 forces the first and
second pinch levers 38, 40 away from the pump inlet 32 and the pump
outlet 34, respectively, the testing instrument 200 is introduced
into the third testing access port 208 and the actuator 102 is
moved into the engaged position to engage and retain the pinch
levers 38, 40 in the open position such that the system 10 is now
prepared for sterilization. It is to be understood by those skilled
in the art that the testing instrument 200 includes male prongs,
generally indicated at 210, introduced into the testing access
ports 204, 206, 208.
[0108] The system 10 further includes at least one controller
access port 212 defined within the base 16. In the preferred
embodiment, the at least one controller access port 212 is defined
within the top housing 22 or cover. The at least one controller
access port 212 is aligned with the electronic controller 118 to
provide access for a second testing instrument 214. It is to be
understood that the second testing instrument 214 and the testing
instrument 200 may be a unitary component, as disclosed in the
Figures. The second testing instrument 214 causes the electronic
controller 118 to activate the motor 42 such that the motor 42 is
powered to alternate the pump inlet 32 and the pump outlet 34
between the open and closed states after assembly and during
testing of the system 10. The second testing instrument 214 also
preferably includes male prongs 210 that are introduced into the
controller access ports 212.
[0109] Referring primarily to FIGS. 2A-3, and 19-20, the system 10
of the present invention is also suitable to be carried by the
patient 12. To facilitate carrying of the system 10 so the patient
12 can remain ambulatory, a carrying strap 216 is mounted within
the base 18 for the carrying of the system 10 by the patient 12. An
integral storage cavity 218 is defined within the base 18. The
carrying strap 216 is at least partially disposed in the integral
storage cavity 218. The carrying strap 216 at least partially
extends from the integral storage cavity 218 to interact with the
patient 12 for carrying the system 10.
[0110] The system 10 further includes a plurality of cavity walls.
The cavity walls extend from the base 18 to define the integral
storage cavity 218 between the base 18 and cover 22. Referring
particularly to FIG. 20, the cavity walls are further defined as a
front wall 220, a rear wall 222, and first and second side walls
224 extending between the front and rear walls 220, 222 to support
the front and rear walls 220, 222 and to define the integral
storage cavity 218. At least one strap slot 226 is defined within
the front wall 220 such that at least a portion, not numbered, of
the carrying strap 216 extends from the integral storage cavity 218
and through the strap slot 226. The patient 12 can then access the
portion of the carrying strap 216 when desired.
[0111] In interacting with the carrying strap 216, the patient 12
simply manipulates, or grabs, the portion of the carrying strap 216
to pull a length of the carrying strap 216 from the integral
storage cavity 218. This length is then looped about the head of
the patient 12 as specifically disclosed in FIG. 19. In the
preferred embodiment, the carrying strap 216 is retractable into
the integral storage cavity 218 after the length has been pulled
from the integral storage cavity 218 by the patient 12. The system
10 further includes a clip 228 that connects opposing ends of the
carrying strap 216 such that the carrying strap 216 is adjustable
to fit patients 12 of all sizes. In the most preferred embodiment
of the present invention, which is disclosed in FIG. 19, the
carrying strap 216 is further defined as a shoulder strap. The
shoulder strap suspends from a shoulder of the patient 12 for
carrying the system 10.
[0112] Also, as particularly disclosed in FIG. 1B, the system 10
may also further include a system mounting clip 230 that extends
from an exterior facing 232 of the base 16. The system mounting
clip 230 can be mounted to a belt 234 of the patient 12. Of course,
it is to be understood that the system mounting clip 230 is not to
be limited to a clip for a belt 234. Instead, the system mounting
clip 230 may be mounted to a shirt, a pocket, and the like.
[0113] With specific reference to FIG. 21, a control system 240 for
the system 10, according to an embodiment of the present invention
is shown. The control system 240 includes the electronic controller
118 and a motor control circuit 242. The electronic controller 118
controls operation of the system 10 as described above.
[0114] In one embodiment, the electronic controller 118 includes a
microprocessor 244. One suitable microprocessor 244 is available
from Philips Semiconductor of Sunnyvale, Calif. as model no.
87LPC764. The electronic controller 118 is programmed to control
operation of the motor control circuit 242 with a computer software
program. In general, the electronic controller 118 generates
control signals in accordance with the computer software program
and delivers the control signals to the motor control circuit
242.
[0115] The motor control circuit 242 includes a first switch 246.
The first switch 246 has an open state and a closed state.
[0116] The control system 240 also includes a watchdog circuit 248
coupled to the electronic controller 118. The watchdog circuit 248
includes a monitor circuit 250 and a second switch 252. The second
switch 252 has an open state and a closed state and is coupled to
the first switch 246. The monitor circuit 250 is adapted to detect
an abnormal condition of the control system 240 and to turn the
second switch 252 off if the abnormal condition is detected.
Examples of an abnormal condition include, but are not limited to,
too many revolutions of the motor 42, failure of the electronic
controller 118, failure of the first switch 246, or failure of a
motor sensor 254 (see below).
[0117] The motor control circuit 242 is adapted to receive control
signals from the electronic controller 118 and to responsively
supply power to the motor 42 by placing the first switch 246 in the
closed state. Power is supplied to the motor 42 if the first and
second switches 246, 252 are in the closed state.
[0118] With reference to FIGS. 22 and 23, in one embodiment the
first and second switches 246, 252 are field effect transistors
(FETs) 256, 258.
[0119] In one embodiment, the control system 240 includes the input
device 176. A user such as a medical professional or the patient 12
is able to program the control system 240 to deliver medication at
the desired flow rate using the input device 176. Based on the
desired flow rate, the electronic controller 118 controls
energization of the motor 42 to deliver the medication.
[0120] In one embodiment, each revolution of the motor 42 delivers
a set amount of the medication during a known period of time. In
order to meet the desired flow rate, the electronic controller 118
calculates a period of time between revolutions of the motor
42.
[0121] In one embodiment, the motor control circuit 242 includes
the motor sensor 254 (see FIG. 4). The motor sensor 254 is coupled
to the motor 42 and is adapted to detect a revolution of the motor
42 and to responsively generate a motor revolution signal in
response to completion of the motor 42 revolution. In one
embodiment, the motor sensor 254 is a opto-coupler sensor which is
adapted to detect the presence of an indicating flag 260 (see FIG.
5) connected to the motor 42. The indicating flag 260 extends from
one of the first and second outside cams 64, 66 to assist in
monitoring the amount of the medication that has been delivered to
the patient 12. The sensor 254 is optically-coupled with the
indicating flag 260 to count revolutions of the indicating flag
260. One suitable sensor 254 is available from Omron of Schaumburg,
Ill., as model no. EE-SX1109.
[0122] In one embodiment, the electronic controller 118 is adapted
to reset the watchdog circuit 248 prior to sending control signals
to the motor control circuit 242 to energize the motor 42. The
watchdog circuit 248 is adapted to place the second switch 252 in
the opened state if two motor revolution signals are received
without the watchdog circuit 248 being reset.
[0123] In other words, the electronic controller 118 must reset the
watchdog circuit 248 prior to or between each revolution of the
motor 42. Thus, if a failure of the electronic controller 118 or
the microprocessor 244 erroneously causes a control signal to be
delivered to the motor control circuit 242 to continuously place
the first switch 246 in the closed state, and thus, to erroneously
energize the motor 42, the second switch 252 will be placed in the
opened state. With the second switch 252 in the opened state, power
will not be delivered to the motor 42.
[0124] Additionally, if a failure of the first switch 246 leaves
the first switch 246 in the closed state, successive motor
revolution signals will be received by the watchdog circuit 248
without the watchdog circuit 248 being reset and the watchdog
circuit 248 will place the second switch 252 in the opened state,
thus preventing power from being supplied to the motor 42.
[0125] In one embodiment, the electronic controller 118 is adapted
to track the time after a motor control signal has been sent and to
enter a disabled state if the time between the sent control signal
and received motor revolution signal exceeds a predetermined
threshold.
[0126] With specific reference to FIG. 22, in one embodiment the
monitor circuit 248 includes first and second flip-flops 262, 264.
The first flip-flop 262 is coupled to the electronic controller 118
and the second flip-flop 264. The second flip-flop 264 is coupled
to the second FET 258.
[0127] In the illustrated embodiment, the first and second
flip-flops 262, 264 are JK flip-flops. The inverse output
({overscore (Q)}) of the second flip-flop 264 is connected to the
gate of the second FET 258. The clock input (CLK) of the second
flip-flop 264 is coupled to the output (Q) of the first flip-flop
262. Power is supplied by the microprocessor 244 to the first and
second flip-flops 262, 264 to the J and K inputs of the first flop
262 and to the J input of the second flip-flop 264. The drain of
the second FET 258 is coupled to the first FET 256 and the source
of the second FET 258 is connected to electrical ground.
[0128] The watchdog circuit 248 is reset by shutting off and
restoring power to the first and second flip-flops 262, 264, to the
J and K inputs of the first flop 262, and to the J input of the
second flip-flop 264. In one embodiment, the electronic controller
118 shuts off power to the first and second flip-flops 262, 264
after each revolution of the motor 42 and supplies power prior to
turning on the first switch 246 to begin the next cycle. This has
two effects: conserving power and resetting the first and second
flip-flops 262, 264.
[0129] The clock input (CLK) of the first flip-flop 262 is
connected to the output of the motor sensor 254. The clock input
(CLK) of the first flip-flop 262 is also connected to the
microprocessor 244 via a third FET 266. The third FET 266 provides
isolation between the microprocessor 244 and the motor sensor 254
and the monitor circuit 248. This isolation prevents a shorted pin
on the electronic controller 118 from preventing revolution pulses
from reaching the flip-flops 262, 264.
[0130] The inverse clear input ({overscore (CLR)}) of the first and
second flip-flops 262, 264 are coupled to the microprocessor 244
via a buffer circuit 268. In the illustrated embodiment, the buffer
circuit 268 includes a first buffer 270, a first resistor 272 and a
capacitor 274. The electronic controller 118 may continuous supply
power to the motor 42 by turning on the first switch 246 and
continuously resetting the first and second flip-flops 262, 264
through the inverse clear inputs without turning off power to the
flip-flops 262, 264.
[0131] In one embodiment, the flip-flops 262, 264 are triggered by
logic level high ("HIGH") to logic level low ("LOW") transitions.
The buffer circuit 268 prevents erroneous signal transitions when
the input to the buffer circuit 268 is held HIGH by the
microprocessor 244.
[0132] With specific reference to FIG. 23, the motor control
circuit 242 includes the first FET 256 and the opto-coupler sensor
276. A flashback diode 278 is coupled across first and second motor
junctions 280A, 280B. The opto-coupler sensor 276 is coupled to the
second motor junction 280B. The transmitting diode of the opto
coupler sensor 276 is coupled to power (V+) and ground through
switch 256. In this arrangement the sensor 276 is only powered
during the time the motor 42 is running thus conserving battery
life. An output of the opto-coupler sensor 276 is coupled to the
third transistor 266 via a second buffer 282.
[0133] The gate of the first FET 256 is coupled to the
microprocessor 244. The drain of the first FET 256 is coupled to
the motor 42 and the source of the first FET 256 is connected to
the drain of the second FET 258.
[0134] As described above, the electronic controller 118 is adapted
to supply medication by energizing the motor 42. A desired flow
rate is achieved by energizing the motor 42 and waiting between
revolutions of the motor 42 for a calculated period of time. The
motor 42 is energized by turning on the first FET 256. In the
illustrated embodiment, the first FET 256 is turned on by the
microprocessor 244 by changing the state of the gate of the first
FET 256 from LOW to HIGH. If the second FET 258 is also on, then
power flows through the motor 42 and the first and second FETs 256,
258. When the motor 42 has made one (1) complete revolution, then
the output of the motor sensor 254 transitions from HIGH to LOW. In
the illustrated embodiment, this transition is the motor revolution
signal. The motor revolution signal is also transmitted to the
microprocessor 244 via the third FET 266. After receiving the motor
revolution signal the microprocessor 244 turns off the first FET
256 by changing the state of the gate of the first FET 256 from
HIGH to LOW.
[0135] During normal operation, the microprocessor 244 then turns
off power to the first and second flip-flops 262, 264. As described
above, based on the desired flow rate and the known quantity of
medication delivered per revolution of the motor 42, the
microprocessor 244 calculates a wait period between motor
revolutions. After the wait period (or right before the wait period
ends), the microprocessor 244 restores power to the first and
second flip-flops 262, 264. As discussed above, this resets the
first and second flip-flops 262, 264. Then the microprocessor 244
may again turn on the first FET 256 to energize the motor 42.
[0136] If a failure condition of the control system 240 exists,
such as a microprocessor 244 failure or other failure, and the
watchdog circuit 248 is not reset, then watchdog circuit 248 turns
off the second FET 258, thereby preventing power from being
supplied to the motor 42.
[0137] For example, if the microprocessor 244 fails while the first
FET 256 is on, then the motor 42 will continue to be energized. The
motor sensor 254 will generate motor revolution signals each time a
motor revolution is completed. However, the microprocessor 244 does
not or is unable to reset the watchdog circuit 248. Two successive
motor revolution signals received on the CLK input of the first
flip-flop 262 without the watchdog circuit 248 being reset will
flip the inverse output of the second flip-flop 264 (from HIGH to
LOW) and thus turn off the second FET 258.
[0138] Likewise, a failure of the first transistor 256 in the
closed state will continuously energize the motor 42. If the
microprocessor 244 does not reset the watchdog circuit 248, then
successive motor revolution signals received on the CLK input of
the first flip-flop 262 will flip the inverse output of the second
flip-flop 264 and thus turn off the second FET 258.
[0139] With the second FET 258 in the off state, power will not be
delivered to the motor 42.
[0140] Returning to FIG. 21, the control system 240 further
includes a key 284 which is connected to the electronic controller
118 only during initialization. In one embodiment, the key 284 is
part of the testing instrument 200, which is also used to test the
control system 240 after it has been assembled and the batteries 45
are installed. Upon initial power-up, the control system 240 will
only initialize if the key 284 is present. If the key 284 is not
present, then the control system 240 enters a disabled mode and
medication cannot be delivered.
[0141] In one embodiment, upon initial power-up the control system
240 sends a signal to the key 284. If present, the key 284 delivers
a return signal to the control system 240 indicating its presence.
The use of the key 284 ensures that the system 10 cannot be
improperly reset by removing and then re-inserting the batteries 45
or other power supply 43. If this occurs and the key 284 is not
present, the system 10 will not work.
[0142] The control system 240 includes a crystal 285 coupled to the
microprocessor 244. The crystal 285 controls the frequency at which
the microprocessor 244 operates in a conventional manner. However,
if the crystal 285 is operating improperly, the microprocessor 244
could begin to operate at either a higher frequency or a lower
frequency than intended. The microprocessor 244 also includes an
internal oscillator 286. In one embodiment, the control system 240
is adapted to compare a frequency of the crystal 285 with a
frequency associated with the internal oscillator 286. The
electronic controller 118 adapted to compare a difference between
the first and second frequencies and enter a disabled state if the
difference is greater than a predetermined threshold. Thus, if the
crystal 285 experiences a failure, the control system 10 will be
disabled.
[0143] Referring to FIGS. 2B, 24, 25A-25F, 26, and 27A-27B, the
present invention further provides a method of controlling the
system 10. This method is designed to be convenient for users,
e.g., medical professionals and/or the patient 12. Referring to
FIG. 24, a removable overlay label 238, having a set of explanatory
indicia, i.e., instructions, is mounted, preferably adhered, to the
system 10. According to the overlay label 238, the method of
setting the system 10 includes first activating the system 10 using
the input device 176, e.g., by depressing any of the touch
sensitive elements 176a-d (hereinafter "buttons" 176a-d), to
activate the system 10. The buttons 176a-d may be touch-sensitive
areas on a touch screen display or raised buttons for depressing.
In other embodiments, the input device 176 may be voice-activated.
Next, using the "select settings" button 176a, the user can scroll
through the operating parameters to be set and use the "adjust
value" button 176b to adjust values of the operating parameters
accordingly. This is illustrated in FIGS. 25A-25D where the value
adjacent to indicia indicating the operating parameter to be set
blinks as the user scrolls through the operating parameters.
[0144] The operating parameters to be set include drug
concentration, flow rate, bolus amount, and bolus lockout time.
These parameters are well known to those skilled in the art and
will not be described in detail, except to say that the bolus
lockout time, once set, and once the system 10 is operating,
includes a countdown timer that begins to countdown from the
established lockout time until zero, with the time remaining
displayed on the display 174. When the display indicates zero time
remaining, another bolus can be delivered to the patient. Other
parameters, not mentioned, could also be set.
[0145] Referring to FIG. 25E, after the operating parameters have
been set, i.e., values for the operating parameters have been
established, the system 10 can be locked such that the operating
parameters are unable to be modified. After the user is satisfied
with his or her selections, the user depresses a "lock/unlock"
button 176c, reviews his or her selections, and then depresses the
lock/unlock button 176c again to lock the settings and activate the
system 10. Once the system 10 is locked, the user can remove the
removable overlay label 238. To accomplish this, the user, either
the medical professional or the patient 12, simply pulls the
removable overlay label 238 off the system 10. The lock/unlock
button 176c is also configured to turn the system 10 on and off, by
depressing the lock/unlock button 176c for a predetermined period
of time, such as five seconds. Once the system 10 is locked, the
system 10 is designed to be convenient for use by the patient
12.
[0146] The system 10, when locked, is configured to prevent the
patient 12 or other persons from altering any of the operating
parameters during use. As a result, the select settings 176a and
adjust value 176b buttons cease to function in the same manner as
when the system 10 was unlocked. In other words, when the
lock/unlock button 176c is depressed to lock the settings, a signal
is transmitted to the controller 118 and the controller 118 alters
the functionality of the buttons 176a-d, as is appreciated by those
skilled in the art, to prevent the user from resetting the
operating parameters. However, in some instances, it is desirable
to allow the user, particularly the medical professional, to reset
the operating parameters, such as when increased delivery rates of
medication are needed by the patient 12. To facilitate this need,
the system 10 is also capable of being unlocked to allow the user
to reset the operating parameters in the manner previously
described. The system 10 uses a code 236 or password, entered using
the input device 176, and transmitted to and received by the
controller 118, to unlock the system 10.
[0147] Referring to FIG. 26, the code 236 is at least periodically
displayed on the display 174 during use. In this embodiment,
periodic can be defined as being at predefined time intervals or at
random times. In a preferred embodiment, the code 236 is
continuously displayed on the display 174 during use. In one
embodiment, the code 236 comprises alphanumeric characters or
values based on or associated with the set values of the operating
parameters, or at least portions thereof. For instance, the set
values for the operating parameters in FIG. 26 include a drug
concentration of 1.00, a flow rate of 12.0 mL per hour, a bolus
amount of 3.0 mL, and at this point in time, the countdown timer of
the bolus lockout time is at 102 minutes. The code 236 comprises
the set values of the operating parameters corresponding to a
predetermined pattern of values as displayed on the display 174. In
FIG. 26, the predetermined pattern is shown by dashed lines. In
this case, the predetermined pattern provides a code 236 of
"0201".
[0148] Since the countdown timer of the bolus lockout time
comprises a portion of the code 236, and the countdown timer
displayed on the display 174 changes with time, then the code 236
also changes with time, or is altered based on a predetermined time
interval. Here, since the first column of the countdown timer is
used to determine the code 236, the code changes every one hundred
minutes while the bolus lockout time is counting down. Other
predetermined time intervals could also be used. Preferably, the
code 236 is altered at least once during use of the system 10.
[0149] Furthermore, the code 236 could also be another combination
or predetermined pattern of the values displayed on the display
174. For instance, still referring to FIG. 26, the code 236 could
be the first column of the set value for concentration, the second
column of the set value for flow rate, the second column of the set
value for bolus amount, and the third column of the countdown
timer. In this instance, the code 236 would be "1232" and would
change every minute. In other words, alternative predetermined
patterns of the alphanumeric characters displayed on the display
174, either continuously, or at least periodically, could be used
to define the code 236.
[0150] Referring to FIGS. 27A and 27B, once the code 236 is
obtained, the user presses the lock/unlock button 176c for a
predetermined time period, preferably less than a second, and the
set values of the operating parameters disappear from the display
174. The user then enters the code 236 into their respective
positions on the display 174 using the select settings 176a and
adjust value 176b buttons. Once the code 236 is entered, the
lock/unlock button 176c is depressed. If the code 236 was entered
properly, the system 10 unlocks to allow the user to reset the
operating parameters as discussed above, including re-locking the
system 10 after the values of the operating parameters are reset.
In other words, when the code 236 is properly entered, the
controller 118 is programmed to reset the functionality of the
buttons 176a-d to allow the user to reset the operating parameters.
If the code 236 is not properly entered, the user is given a
predetermined number of unsuccessful entry attempts in a
predetermined time period, such as five attempts in thirty minutes.
If the number of unsuccessful attempts exceeds the predetermined
number, the input device 176 will be locked for a predetermined
time period before allowing further attempts to enter the code 236.
In other words, the user will be restricted from entering the code
236 for the predetermined time period.
[0151] In operating the system 10, the system 10 may be
deactivated, if necessary, to stop delivery of the medication to
the patient 12. To deactivate the system 10, the patient 12
depresses the lock/unlock button 176c as described above. If the
system 10 is deactivated, then the patient 12 may also use the
lock/unlock button 176c to activate the system 10 to re-start
delivery of the medication to the patient 12.
[0152] In operating the system 10, the patient 12 may request an
additional amount of the medication relative to the selected amount
of the medication, and provided the bolus amount will not be
violated, the patient 12 will receive an additional amount of the
medication. To request an additional amount of the medication
relative to the selected amount, the patient 12 actuates a bolus
button 176d. Those skilled in the art appreciate that the
controller 118 is programmed in a known manner to carry out these
and other functions of the system 10.
[0153] Referring to FIGS. 28-39, the refill port 300 is shown. By
using the refill port 300, the fluid, e.g., medication, can be
added to the reservoir 24 such that the system 10 is more suitable
for procedures in which large quantities of medication are
required, without disconnecting the infusion tube set 14 from the
port 82. Referring specifically to FIGS. 29 and 30, the refill port
300 includes a slit-type swabable valve 302 such as the valve shown
in U.S. Pat. No. 6,651,956, hereby incorporated by reference, and
commercially available from Halkey-Roberts Corporation of St.
Petersburg, Fla. The valve 302 is mounted to the base 18 such that
a valve stem 304 with slit (or other penetrable septum member) is
accessible from a bottom of the system 10, as shown in FIG. 28. A
removable port cap 303 is attached to the base 18 by a leash 307
for covering the valve stem 304 when not in use.
[0154] With reference to FIG. 29, the valve 302 includes three
basic components, a luer body 330, the valve stem 304, and a valve
body 324. The luer body 330 and the valve stem 304 are further
discussed in the '956 patent incorporated herein. The valve body
324 of the valve 302 includes upper 326a and lower 326b tabs and
snap-lock fingers 328 to secure the valve body 324 to the base 18
of the system 10. FIG. 30 illustrates the valve body 324 mounted to
the luer body 300 such as by ultrasonic welding, adhesive, or the
like. The valve stem 304 is captured between the valve body 324 and
the luer body 300.
[0155] With reference to FIGS. 31 and 32, a valve mount 316 is
integrally formed in the base 18 to mount the valve body 324 to the
base 18. The valve mount 316 is designed with a low profile.
Referring to FIGS. 33-35, the valve mount 316 includes notches 318
and a groove 320 for receiving the lower tabs 326b of the valve
body 324. The valve mount 316 also includes cammed portions 322a,
322b to rotatably and axially lock the valve body 324 to the valve
mount 316. More specifically, the upper 326a and lower 326b tabs
and snap-lock fingers 328 of the valve body 324 co-act with the
notches 318, groove 320, tab guides 321, and cammed portions 322a,
322b of the valve mount 316 to secure the valve body 324 to the
valve mount 316 in a snap-locked manner to rotationally and axially
restrain the valve body 324 to the base 18.
[0156] In FIGS. 33-35, the valve body 324 is inserted into the
valve mount 316, but not yet locked in position. The lower tabs
326b of the valve body 324 are lowered through the notches 318 and
springably slide over the cammed portions 322a in the valve mount
316 such that the lower tabs 326b rest in the groove 320. The upper
tabs 326a rest above an upper surface of an outside wall 329 of the
valve mount 316.
[0157] In FIGS. 36-38, the valve body 324 is shown rotated
counter-clockwise relative to the valve mount 316 to snap-lock the
valve body 324 to the valve mount 316. Here, the snap-lock fingers
328 (which include cammed edges) ride over the cammed portions 322b
of the valve mount 316 and snap-lock into position to prevent any
clockwise rotation. The shape of the snap lock fingers 328 is
optimized to stay below stress yield points during insertion into
their snap-locked positions, while retaining sufficient rigidity to
prevent disassembly during syringe removal. At the same time, the
lower tabs 326b abut stops (not shown) in the valve mount 316 to
prevent any further counter-clockwise rotation. As a result, the
valve body 324 is rotatably locked relative to the valve mount 316.
Simultaneously, the lower tabs 326b ride below the tab guides 321
of the valve mount 316 to prevent any further axial movement of the
valve body 324 relative to the valve mount 316 in one direction,
while the upper tabs 326a rest above the outside wall 329 of the
valve mount 316 to prevent axial movement in the opposite
direction.
[0158] Referring to FIG. 39, a flanged connector 301 is used to
provide fluid communication between the valve 302 and the reservoir
24. As shown, an opening 297 is formed in one side of the reservoir
24 (shown here in a deflated state). The flanged connector 301,
which includes a flange 303 and a stem 305 having an opening 299
defined therethrough, is secured to the reservoir 24 at the opening
297. More specifically, the flange 303 is ultrasonically welded, or
adhered using an adhesive or other methods, to the reservoir while
the openings 297, 299 are aligned to provide fluid communication
with an interior of the reservoir 24. Once the flanged connector
301 is fixed to the reservoir 24, the stem 305 is inserted into an
orifice 341 defined through the valve body 324 and secured thereto
by ultrasonic welding, adhesive, or the like. This step usually
occurs after the valve body 324 is snap-locked to the valve mount
316. As a result, the reservoir 24 is placed in fluid communication
with the valve stem 304 such that when a fluid filling device, such
as a syringe S, is attached to the luer body 330, the syringe
penetrates the slit in the valve stem 304 and fluid communication
is provided between the syringe S and the reservoir 24 to refill
the reservoir 24 of the system 10.
[0159] In addition to any fluid holding capability of the valve
stem 304, a one-way valve, such as a duck-billed valve 311 shown in
FIG. 37, may be mounted (ultrasonically welded, adhered, etc.)
inside the stem 305 or at some other convenient location to prevent
the fluid from leaking out of the refill port 300.
[0160] During use, the port cap 303 is first removed from the
refill port 300. Then, the valve stem 304 is swabbed for sterility
per standard protocol. The syringe S is then filled with the fluid,
e.g., medication, and once excess air is removed from the syringe
S, the syringe S is luer-locked to luer body 330 and the fluid
transferred from the syringe S into the reservoir 24. This can be
repeated until the reservoir 24 is refilled. Once complete, the
port cap 303 is replaced. If the system 10 is displaying the empty
symbol on the display 174, the lock/unlock button 176c can be
depressed to reactivate the system 10.
[0161] Obviously, many modifications and variations of the present
invention are possible in light of the above teachings. Also, it is
to be understood that reference numerals are merely for convenience
and are not to be in any way limiting.
* * * * *